EP3253442B1 - Apparatus for providing cardiac pacing with electrode selection according to heart rate - Google Patents

Apparatus for providing cardiac pacing with electrode selection according to heart rate Download PDF

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Publication number
EP3253442B1
EP3253442B1 EP16704342.1A EP16704342A EP3253442B1 EP 3253442 B1 EP3253442 B1 EP 3253442B1 EP 16704342 A EP16704342 A EP 16704342A EP 3253442 B1 EP3253442 B1 EP 3253442B1
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EP
European Patent Office
Prior art keywords
pacing
electrodes
electrode
heart rate
circuit
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EP16704342.1A
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German (de)
English (en)
French (fr)
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EP3253442A2 (en
Inventor
David J. Ternes
William J. Linder
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Cardiac Pacemakers Inc
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Cardiac Pacemakers Inc
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A61N1/3686—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions configured for selecting the electrode configuration on a lead
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056—Transvascular endocardial electrode systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/36514—Heart stimulators controlled by a physiological parameter, e.g. heart potential controlled by a physiological quantity other than heart potential, e.g. blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A61N1/3682—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions with a variable atrioventricular delay
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A61N1/3684—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions for stimulating the heart at multiple sites of the ventricle or the atrium
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A61N1/3684—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions for stimulating the heart at multiple sites of the ventricle or the atrium
    • A61N1/36842—Multi-site stimulation in the same chamber
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/368—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions
    • A61N1/3684—Heart stimulators controlled by a physiological parameter, e.g. heart potential comprising more than one electrode co-operating with different heart regions for stimulating the heart at multiple sites of the ventricle or the atrium
    • A61N1/36843—Bi-ventricular stimulation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/37—Monitoring; Protecting
    • A61N1/3702—Physiological parameters

Definitions

  • Ambulatory medical devices include implantable medical devices (IMDs) and wearable medical devices.
  • IMDs include cardiac function management (CFM) devices such as implantable pacemakers, implantable cardioverter defibrillators (ICDs), cardiac resynchronization therapy devices (CRTs), and devices that include a combination of such capabilities.
  • CFM cardiac function management
  • ICDs implantable cardioverter defibrillators
  • CRTs cardiac resynchronization therapy devices
  • the devices can be used to treat patients or subjects using electrical or other therapy, or to aid a physician or caregiver in patient diagnosis through internal monitoring of a patient's condition.
  • the devices may include one or more electrodes in communication with one or more sense amplifiers to monitor electrical heart activity within a patient, and often include one or more sensors to monitor one or more other internal patient parameters.
  • wearable medical devices include wearable cardioverter defibrillators (WCDs) and wearable diagnostic devices (e.g., an ambulatory monitoring vest).
  • WCDs can be monitoring devices that include surface electrodes.
  • the surface electrodes may be arranged to provide one or both of monitoring to provide surface electrocardiograms (ECGs) and delivery of cardioverter and defibrillator shock therapy.
  • ECGs surface electrocardiograms
  • a wearable medical device can also include a monitoring patch worn by the patient such as an adherable patch or a patch included with an article of clothing worn by the patient.
  • ambulatory medical devices are typically optimized by a caregiver, such as by programming different operating parameters of the medical device for example.
  • Manufacturers of such devices continue to improve and add functionality to the devices, which can make them complicated to program and optimize to the needs of a particular patient.
  • the inventor has recognized a need for improved optimization of device-based therapy.
  • the present subject matter relates to providing multi-site pacing therapy in a manner that minimizes complexity of the resulting interactive parameter limits.
  • an apparatus for coupling to a plurality of electrodes implantable at a plurality of tissue sites of a heart chamber of a subject includes a stimulus circuit configured to provide an electrical cardiac pacing stimulation to the plurality of electrodes, a switching circuit configured to select electrodes of the plurality of electrodes for electrical coupling to the stimulus circuit, and a control circuit including a heart rate sub-circuit configured to determine heart rate; and a pacing site activation sub-circuit configured to selectively change which electrodes of the plurality of electrodes are used to provide the electrical cardiac pacing stimulation therapy according to the determined heart rate.
  • An ambulatory medical device can include one or more of the features, structures, methods, or combinations thereof described herein.
  • a cardiac monitor or a cardiac stimulator may be implemented to include one or more of the advantageous features or processes described below. It is intended that such a monitor, stimulator, or other implantable or partially implantable device need not include all of the features described herein, but may be implemented to include selected features that provide for unique structures or functionality. Such a device may be implemented to provide a variety of therapeutic or diagnostic functions.
  • FIG. 1 is an illustration of portions of a system that includes an IMD 110.
  • IMD 110 include, without limitation, a pacemaker, a defibrillator, a cardiac resynchronization therapy (CRT) device, or a combination of such devices.
  • the system also typically includes an IMD programmer or other external device 170 that communicates wireless signals 190 with the IMD 110, such as by using radio frequency (RF) or other telemetry signals.
  • RF radio frequency
  • the IMD 110 can be coupled by one or more leads 108A-C to heart 105.
  • Cardiac leads 108A-C include a proximal end that is coupled to IMD 110 and a distal end, coupled by electrical contacts or "electrodes" to one or more portions of a heart 105.
  • the electrodes typically deliver cardioversion, defibrillation, pacing, or resynchronization therapy, or combinations thereof to at least one chamber of the heart 105.
  • the electrodes may be electrically coupled to sense amplifiers to sense electrical cardiac signals.
  • Sensed electrical cardiac signals can be sampled to create an electrogram.
  • An electrogram can be analyzed by the IMD and/or can be stored in the IMD and later communicated to an external device where the sampled signals can be displayed for analysis.
  • Heart 105 includes a right atrium 100A, a left atrium 100B, a right ventricle 105A, a left ventricle 105B, and a coronary sinus 120 extending from right atrium 100A.
  • Right atrial (RA) lead 108A includes electrodes (electrical contacts, such as ring electrode 125 and tip electrode 130) disposed in an atrium 100A of heart 105 for sensing signals, or delivering pacing therapy, or both, to the atrium 100A.
  • RV lead 108B includes one or more electrodes, such as tip electrode 135 and ring electrode 140, for sensing signals, delivering pacing therapy, or both sensing signals and delivering pacing therapy.
  • RV lead 108B can include one or more additional ring electrodes 142 to provide multi-site pacing the RV.
  • Lead 108B optionally also includes additional electrodes, such as electrodes 175 and 180, for delivering atrial cardioversion, atrial defibrillation, ventricular cardioversion, ventricular defibrillation, or combinations thereof to heart 105. Such electrodes typically have larger surface areas than pacing electrodes in order to handle the larger energies involved in defibrillation.
  • Lead 108B optionally provides resynchronization therapy to the heart 105. Resynchronization therapy is typically delivered to the ventricles in order to better synchronize the timing of depolarizations between ventricles.
  • the IMD 110 can include a third cardiac lead 108C attached to the IMD 110 through the header 155.
  • the third cardiac lead 108C includes electrodes 160, 162, 164, and 165 placed in a coronary vein 122 lying epicardially on the left ventricle (LV) 105B via the coronary vein.
  • the number of electrodes shown in the Figure is only an example and other arrangements are possible.
  • the third cardiac lead 108C may include less electrodes (e.g., one or two electrodes) or more electrodes (e.g., eight or more electrodes) than the example shown, and may include a ring electrode 185 positioned near the coronary sinus (CS) 120.
  • CS coronary sinus
  • the IMD 110 can include a fourth cardiac lead 108D that includes electrodes 187 and 189 placed in a vessel lying epicardially on the left atrium (LA) 100B.
  • LA left atrium
  • the IMD 110 can include a hermetically-sealed IMD housing or can 150, and the IMD 110 can include an electrode 182 formed on the IMD can 150.
  • the IMD header 155 may also include an electrode 184.
  • Cardiac pacing therapy can be delivered in a unipolar mode using the electrode 182 or electrode 184 and one or more electrodes formed on a lead.
  • Cardiac pacing therapy can be delivered in an extended bipolar pacing mode using only one electrode of a lead (e.g., only one electrode of LV lead 108C) and one electrode of a different lead (e.g., only one electrode of RV lead 108B).
  • Cardiac pacing therapy can be delivered in a monopolar pacing mode using only one electrode of a lead without a second electrode.
  • Lead 108B can include a first defibrillation coil electrode 175 located proximal to tip and ring electrodes 135, 140 for placement in a right ventricle, and a second defibrillation coil electrode 180 located proximal to the first defibrillation coil 175, tip electrode 135, and ring electrode 140 for placement in the superior vena cava (SVC).
  • SVC superior vena cava
  • high-energy shock therapy is delivered from the first or RV coil 175 to the second or SVC coil 180.
  • the SVC coil 180 is electrically tied to the electrode 182 formed on the IMD can 150. This improves defibrillation by delivering current from the RV coil 175 more uniformly over the ventricular myocardium.
  • the therapy is delivered from the RV coil 175 only to the electrode 182 formed on the IMD can 150.
  • the coil electrodes 175, 180 are used in combination with other electrodes for sensing signals.
  • An IMD can be configured with a variety of electrode arrangements including transvenous, endocardial, and epicardial electrodes (e.g., an epicardial patch that may include dozens of electrodes), and/or subcutaneous, non-intrathoracic electrodes. Any of the implantable leads described may include more than the number of leads shown.
  • An IMD 110 can be connectable to subcutaneous array or lead electrodes (e.g., non-intrathoracic electrodes or additional LV leads implantable along the LV wall, and leads implantable in one or both atria) that can be implanted in other areas of the body to help "steer" electrical currents produced by IMD 110.
  • An IMD can be leadless (e.g., a leadless pacemaker).
  • a leadless IMD may be placed in a heart chamber (e.g., RV or LV) and multiple electrodes of the leadless IMD may contact cardiac tissue.
  • the present methods and systems will work in a variety of configurations and with a variety of electrodes.
  • a CRM device may provide multi-site pacing, in which pacing pulses are provided to multiple sites within a same heart chamber. This may be useful to improve coordination of a contraction of a heart chamber, especially of the left ventricle.
  • pacing may be provided to left ventricular electrodes 160, 162, 164, 165 in a specified sequence to coordinate activation at different tissue sites of the left ventricle to a cause a left ventricular (LV) contraction in a desired fashion.
  • RV right ventricular
  • LV3 LV electrode 164
  • LV4 LV3 and LV electrode 162
  • the time delays may be the same or may be individually programmable.
  • Electrode activation may take place in a different order than from LV1 to LV4.
  • Electrodes are also used to sense intrinsic electrical cardiac activity such as intrinsic depolarization to trigger electrical pacing therapy and to sense cardiac tachyarrhythmia which may trigger delivery of anti-tachyarrhythmia therapy.
  • Sensing time windows for cardiac activity detection are enabled in a specified relation to paced events to avoid misidentifying a paced cardiac depolarization as intrinsic activity.
  • the sensing time windows may be enabled after one or both of a blanking period and a refractory period after pacing stimulation is delivered.
  • the multi-site pacing may have an impact on these detection windows.
  • a caregiver may program a CRM device to have a resting heart rate of sixty beats per minute (60bpm), corresponding to a maximum rate interval of 1000 milliseconds (ms).
  • the caregiver may also program a refractory period of 135ms for a total of 415ms.
  • FIG. 2 shows a flow diagram of an example of a method 200 of operating an implantable or otherwise ambulatory medical device.
  • electrical cardiac pacing stimulation therapy is provided to a subject using a set of a plurality of implantable electrodes.
  • pacing stimulation therapy is provided to multiple sites within the left ventricle of the subject.
  • the heart rate may be a measured intrinsic heart rate, or the heart rate may be an activity-based pacing rate calculated or otherwise determined by the medical device.
  • the electrodes that are included in the set of electrodes to provide the electrical cardiac pacing stimulation therapy is selectively changed according to the determined heart rate.
  • the heart rate increases (e.g., to a first specified heart rate threshold)
  • one or more of the electrodes can be removed from the set used to deliver therapy.
  • the heart rate decreases (e.g., below the threshold)
  • electrodes can be replaced in the set used to deliver therapy.
  • Inter-ventricular delay e.g., RV-LV1 delay
  • Intra-ventricular delays can also be reduced with an increase in heart rate.
  • the intra-ventricular electrodes remaining in use can be educed (e.g., from 10ms to 5ms) to increase time available for a sensing time window.
  • FIG. 3 shows a block diagram of portions of an example of an implantable or otherwise ambulatory medical device.
  • the device 300 includes a stimulus circuit 305 that provides electrical cardiac pacing stimulation to a plurality of electrodes.
  • the electrodes are implantable at a plurality of tissue sites of one or both ventricles of a heart of a subject. Examples of such electrodes were described previously in regard to FIG. 1 .
  • the device 300 includes a switching circuit 310 that selects electrodes for electrical coupling to the stimulus circuit.
  • the device 300 also includes a control circuit 315.
  • the control circuit 315 can include a microprocessor, a digital signal processor, application specific integrated circuit (ASIC), or other type of processor, interpreting or executing instructions included in software or firmware.
  • the control circuit 315 can include other circuits and sub-circuits to perform the functions described. These circuits and sub-circuits may include software, hardware, firmware or any combination thereof. Multiple functions can be performed in one or more of the circuits and sub-circuits as desired.
  • the device 300 includes a cardiac signal sensing circuit 330 that senses electrical cardiac activity signal via the electrodes.
  • the control circuit 315 may use signals that are sensed during a sensing time window of a cardiac cycle to determine device behavior.
  • the control circuit 315 uses the sensed cardiac signals to detect intrinsic activity that affects pacing behavior. For example, sensed atrial activity may be used to time delivery of pacing stimulation to one or both ventricles, and sensed ventricular activity may be used to inhibit pacing or time a pacing stimulation provided to the other ventricle (e.g., cardiac resynchronizaton therapy).
  • control circuit 315 uses the sensed cardiac signals to detect arrhythmia such as cardiac tachyarrhythmia and to initiate delivery of one or more of anti-tachycardia pacing therapy, cardioversion therapy, and defibrillation therapy. Based on the electrode change the control circuit 315 may be able to adjust the specified sensing time window.
  • the electrodes include multiple electrodes implantable in the left ventricle (LV).
  • the device 300 may include a pacing delay sub-circuit 335 that determines a time delay between delivery of a pacing stimulus pulse to a first electrode at a first pacing site of the LV and delivery of a pacing pulse to a second electrode at a second pacing site of the LV.
  • the pacing delay sub-circuit 335 may determine a time delay between any of LV tip electrode 165, LV electrode 160, LV electrode 164, and LV electrode 162 in FIG. 1 .
  • the pacing site activation sub-circuit 325 may change which of the electrodes are used to provide pacing stimulus pulses to the left ventricle according to the determined heart rate.
  • Electrode LV1 is activated at about 5ms after the RV activity (RV-LV1 delay) and the vertical bar positioned at 10ms represents activation for the LV1 electrode.
  • the graph of FIG. 4 shows an example of the heart rate thresholds above the LRL at which pacing activation sites are dropped. From 60bpm until 80bpm, four pacing stimuli are delivered to the LV at about 10ms, 20ms, 40ms and 60ms. Above 80bpm, the LV4 electrode is dropped from the pacing regimen. From 81bpm until 95bpm three pacing stimuli are delivered to the LV. Above 95bpm, electrode LV3 is dropped. From 96bpm until 110bpm two pacing stimuli are delivered to the LV at about 10ms and 20ms. At heart rates above 111bpm, electrode LV2 is dropped and one pacing stimuli is delivered at about 10ms.
  • the electrodes are reactivated according to the sensing time window available. For instance, electrode LV3 may not be re-activated until a heart rate less than 95bpm so that a specified sensing time window can be provided.
  • a sensing time window may be adjusted according to a determined heart rate that may be a sensed intrinsic rate or a calculated paced rate. Different electrode activations may be used for paced and sensed rates. For instance, it may be desired for one or both of a blanking period and refractory period to be longer for a paced event. This may lead to deactivation of more electrodes at a paved rate to make more time available for the sensing time window.
  • electrode activation may be different for sensed atrial or ventricular events versus paced atrial or ventricular events.
  • electrode activation may be different for a ventricular heart rate that is tracking events in the atrium versus a heart rate that is sensor driven (e.g., driven by patient physical activity).
  • the pacing site activation sub-circuit may recurrently (e.g., periodically) drop one or more paces by the electrodes to allow even longer time for a sensing time window in order to detect intrinsic cardiac activity. This may be useful to avoid delivering pacing stimuli that masks intrinsic cardiac events.
  • the pacing site activation sub-circuit 325 may deliver the pacing stimulus at 35ms with the LV3 electrode electrically coupled to the LV4 electrode.
  • the pacing site activation sub-circuit 325 may change to separate activation of the LV3 and LV4 electrodes when the heart rate decreases below the threshold or below a hysteretic threshold.
  • the pacing site activation sub-circuit 325 changes delivery of the pacing stimulation therapy from a first unipolar pacing mode in which the pacing stimulation is delivered using a can electrode and a sequence of individual electrodes implantable in the left ventricle to a second bipolar pacing mode in which the electrical pacing stimulation therapy is delivered using two LV electrodes. For instance, when the heart rate increases above the 80bpm threshold, the pacing site activation sub-circuit 325 may change from a unipolar pacing mode, in which pacing pulses are delivered between one or more of the LV electrodes in FIG.
  • the pacing site activation sub-circuit 325 may change from a unipolar pacing mode to a tripolar mode with electrode L4 as the pacing anode and electrode L2 electrically coupled to electrode L3 as the pacing cathode.
  • the mode change can be useful to increase the time available for a sensing time window and to improve sensing through the combined electrode.
  • FIG. 5 shows a flow diagram of another example of a method 500 of operating an implantable or otherwise ambulatory medical device.
  • electrical cardiac pacing stimulation therapy is provided to a subject using a set of a plurality of implantable electrodes.
  • the implantable electrodes can include multiple implantable electrodes arranged at multiple tissue sites within one heart chamber of the subject.
  • pacing stimulation therapy is provided to multiple sites within the left ventricle of the subject.
  • the heart rate may be a measured intrinsic heart rate, or the heart rate may be an activity-based pacing rate calculated or otherwise determined by the medical device.
  • the sensing time window is adjusted by changing the activation of the electrodes.
  • the time available for a sensing time window can be changed by activating and deactivating electrodes, by grouping electrodes together for activation, and by changing between unipolar and bipolar pacing modes.
  • the time available for a sensing time window can also be changed by scaling the delay time between electrode activations according to the heart rate.
  • the pacing delay sub-circuit 335 of FIG. 3 changes the intra-ventricular time delay between delivery of a pacing pulse to an electrode arranged at a first ventricular tissue site and an electrode arranged at a second tissue site of the same ventricle.
  • FIG. 6 shows a graph that illustrates an example of a medical device automatically changing electrode activation times according to heart rate.
  • the medical device may include two or more of LV electrode 165 (LV1), LV electrode 160 (LV2), LV electrode 164 (LV3), and LV electrode 162 (LV4) in FIG. 1 .
  • more than four LV electrodes are included with the device.
  • the intra-ventricular delay between activation of electrodes arranged in the LV is uniform. The time delay is about 16ms at the LRL and decreases linearly to about 8ms at the MPR. Decreasing the intra-ventricular time delay provides more time available for a sensing time window.
  • scaling the time delay may add 8ms for a sensing time window. If there are six LV electrodes, scaling the time delay may add 40ms (i.e., 5 X 8ms) for a sensing time window at the MPR.
  • the slope of the line 605 in FIG. 6 is determined by the time delay at the LRL and the time delay at the MPR.
  • the scaling of the time delay may be determined by specifying (e.g., programming) one or more of a time delay at the LRL, a time delay at the MPR, and the slope.
  • multiple slopes are used in the scaling by specifying additional and points of the line or additional slopes.
  • the pacing delay sub-circuit 335 of FIG. 3 changes the inter-ventricular (V-V) time delay according to the determined heart rate.
  • the time delay can be changed between delivery of a pacing pulse to an electrode arranged at a tissue site of a first ventricle and an electrode arranged at a tissue site of the second ventricle (e.g., either RV-LV or LV-RV) to adjust time available for a sensing time window.
  • scaling the V-V time delay may add 30ms for a sensing time window at the MPR. This may be in addition to time made available by scaling any intra-ventricular time delays.
  • the pacing delay sub-circuit 335 of FIG. 3 changes the atrial-to-ventricular (A-V) time delay according to the determined heart rate.
  • scaling the A-V time delay may add 100ms for a sensing time window at the MPR. This may be in addition to time made available by scaling one or both of any intra-ventricular time delays and any inter-ventricular time delay.
  • FIG. 7 shows four sloped lines.
  • the sloped lines intersect the horizontal axis at 10ms, 20ms, 40ms, and 60ms to represent activation times at the LRL for electrodes LV1, LV2, LV3, and LV4 respectively.
  • the intra-ventricular time delay between activation of the LV3 electrode and LV4 electrode (LV3-LV4 delay) is decreased from 20ms. The time delay continues to be decreased until activation of the LV4 electrode is dropped above 80bpm.
  • the time delay between activation of the LV2 electrode and LV3 electrode is decreased from 20ms. The time delay continues to be decreased until activation of the LV3 electrode is dropped above 95bpm.
  • the time delay between activation of the LV1 electrode and LV2 electrode is decreased from 10ms. The time delay continues to be decreased until activation of the LV3 electrode is dropped above 110bpm.
  • RV-LV1 delay For the sloped line for LV1, as the heart rate increases above the LRL, the time delay between activation of the RV and LV1 electrode (RV-LV1 delay) is decreased from 10ms to 7ms at the MPR. Electrodes may be reactivated at the heart rates at which they were deactivated or hysteresis may be used when reactivating an electrode.
  • FIG. 8 illustrates another example of a medical device automatically changing electrode activation and times of activation according to heart rate.
  • an atrial pace stimulus Ap is delivered.
  • the Ap may be delivered according to a device-determined pacing rate.
  • a right ventricle pace stimulus RV P is delivered.
  • a specified inter-ventricular (V-V) delay a left ventricular pace stimulus (LV1) is delivered.
  • Pacing stimuli are then delivered to pacing electrodes LV2, LV3, LV4 at corresponding pacing sites based on intra-ventricular delays.
  • the device determined paced heart rate is increased.
  • the A-V delay from A P -RV P is shown shortened according to heart rate.
  • the middle timing diagram 810 also shows that the LV1 electrode is dropped from the pacing regimen. If the example in FIG. 8 corresponds to the behavior of the device of the example of FIG. 1 , pacing therapy may be delivered in a unipolar pacing mode. Pacing therapy may be delivered to the right atrium using lead electrode 130 and can electrode 182. Pacing therapy may be delivered to the right ventricle using lead electrode 135 and can electrode 182.
  • Multi-site pacing therapy may be delivered to the left ventricle using lead electrode 162 (LV1) and the can electrode 182, lead electrode 164 (LV2) and the can electrode 182, lead electrode 160 (LV3) and the can electrode 182, and lead electrode 165(LV4) and the can electrode 182. Electrode LV1 may be dropped first because of its location closest to the device can.
  • FIG. 9 is an illustration of portions of a system 900 that uses a deployed IMD 910 to provide a therapy to a patient 902.
  • the system 900 typically includes an external device 970 that communicates with a remote system 996 via a network 994.
  • the network 994 can be a communication network such as a cellular phone network or a computer network (e.g., the internet).
  • the external device 970 includes a repeater and communicated via the network using a link 992 that may be wired or wireless.
  • the remote system 996 provides patient management functions and may include one or more servers 998 to perform the functions.
  • the remote system 996 provides electrode activation information for use with the methods of multi-site pacing described previously.

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EP16704342.1A 2015-02-05 2016-02-02 Apparatus for providing cardiac pacing with electrode selection according to heart rate Active EP3253442B1 (en)

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US201562112192P 2015-02-05 2015-02-05
PCT/US2016/016086 WO2016126654A2 (en) 2015-02-05 2016-02-02 Sensing window management of multipoint pacing

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US10603496B2 (en) 2016-11-09 2020-03-31 Cardiac Pacemakers, Inc. Conduction pathway driven multi-site pacing management
CN111295225B (zh) * 2017-11-02 2024-04-19 心脏起搏器股份公司 用于识别希氏束起搏捕获的系统
US11278727B2 (en) * 2017-11-22 2022-03-22 Medtronic, Inc. Efficient delivery of multi-site pacing
CN109745619A (zh) * 2019-01-23 2019-05-14 深圳大学 心脏起搏器控制系统和控制方法

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WO2016126654A3 (en) 2016-10-13
CN107405494B (zh) 2020-09-01
CN107405494A (zh) 2017-11-28
US20160228709A1 (en) 2016-08-11
EP3253442A2 (en) 2017-12-13
US9757569B2 (en) 2017-09-12
WO2016126654A2 (en) 2016-08-11

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